Short communicationAn ultrasound based non-invasive method for the measurement of intrinsic foot kinematics during gait
Introduction
The intrinsic kinematics of the foot are of interest for a number of clinical conditions, and this has been reflected in the large number of multi-segment foot models for motion analysis reported in the literature over the past two decades (Bishop et al., 2012). These models tend to be based on skin mounted marker sets, however studies using bone pins have demonstrated significant differences between the true motion of the foot bones and the motion measured using skin mounted markers (Nester et al., 2007). This error is due in part to movement of the surrounding soft tissue relative to the underlying bony landmarks. In addition, the accuracy of marker placement over the chosen landmark has also been shown to be a potential source of error when measuring foot kinematics (Telfer et al., 2010).
There are primarily two reported methods that allow the direct measurement of bone positions when assessing the intrinsic motion of the foot during dynamic activity: bone pins (Nester, 2009) and fluoroscopy (Shultz et al., 2011). These methods however require invasive surgery or exposure of the patient to ionising radiation respectively, potentially limiting their utility for clinical and large scale research applications.
The aim of this study is to demonstrate a non-invasive method which combines ultrasound and motion capture (US/MC) to directly measure skeletal motion during gait and therefore negate STA and marker placement error when measuring selected foot kinematic parameters, and to compare this method to measurements made using a standard protocol with skin mounted markers.
Section snippets
Participants
Fourteen healthy participants, 7♀, age 37.9 years (SD 12.4), height 1.74 m (SD 0.08) and weight 75 kg (SD 11.3) gave informed, written consent to participate in this study. Ethical approval was obtained from the institutional review board prior to the study commencing (reference HLS12/43).
Equipment
Using sampling frequencies of 120 Hz, an 8 camera motion capture system (Opus 3; Qualisys, Gothenburg, Sweden) was used to track retroreflective markers and a force plate embedded in the walkway (Type 9286B;
Results
Motion/time curves for MLA angle and navicular height determined using the two methods are presented in Fig. 3. Significant differences were found between minimum navicular height determined via the two methods, with the standard protocol estimating the height to be 49.1 mm compared to 45.1 mm for the US/MC technique (P=0.004, 95% CI (1.57, 6.54)). Maximum MLA during stance was significantly different between methods (P=0.0034, 95% CI (13.8, 3.4)) with the standard protocol estimating this angle
Discussion
In comparison to the more proximal joints in the lower limb, the relative motion between the bones of the foot is small even in the primary plan of movement. Therefore the impact of STA and other sources of error in motion analysis of the foot is an important issue, with inaccurate measurements potentially clouding the identification of clinically relevant changes to kinematic variables. In particular, the NT landmark is used in a number of multi-segment foot models (Carson et al., 2001, Hyslop
Conflict of interest statement
The authors declare that they have no conflict of interest relating to the material presented in this article.
Acknowledgements
This work was funded in part through the European Commission Framework Seven Programme (Grant number NMP2-SE-2009–228893) as part of the A-FOOTPRINT project (www.afootprint.eu). The funders had no input into the study design, collection, analysis and interpretation of data; the writing of the manuscript; or the decision to submit for publication.
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